EP0956744B1 - Variable current ct scanning - Google Patents

Variable current ct scanning Download PDF

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Publication number
EP0956744B1
EP0956744B1 EP98900988A EP98900988A EP0956744B1 EP 0956744 B1 EP0956744 B1 EP 0956744B1 EP 98900988 A EP98900988 A EP 98900988A EP 98900988 A EP98900988 A EP 98900988A EP 0956744 B1 EP0956744 B1 EP 0956744B1
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EP
European Patent Office
Prior art keywords
modulation function
data
sector
angular sector
radiation
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Expired - Lifetime
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EP98900988A
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German (de)
English (en)
French (fr)
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EP0956744A1 (en
Inventor
Ehud Dafni
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Philips Medical Systems Technologies Ltd
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Picker Medical Systems Ltd
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05G—X-RAY TECHNIQUE
    • H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
    • H05G1/08—Electrical details
    • H05G1/26—Measuring, controlling or protecting
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05G—X-RAY TECHNIQUE
    • H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
    • H05G1/08—Electrical details
    • H05G1/26—Measuring, controlling or protecting
    • H05G1/30—Controlling
    • H05G1/36—Temperature of anode; Brightness of image power
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral

Definitions

  • the present invention relates generally to computerized tomographic (CT) imaging systems, and specifically to methods for controlling the radiation dosage to which patients are exposed during CT scanning.
  • CT computerized tomographic
  • CT scanners form images based on measurement of X-ray attenuation along multiple paths through the body of a subject.
  • the body is generally irradiated from one side by an X-ray tube, driven by a high-voltage power supply (HVPS), as is known in the art.
  • HVPS high-voltage power supply
  • the X-rays are received by detectors on the opposite side of the body from the tube, which detectors generate signals proportional to the attenuated radiation flux that is incident thereon.
  • the tube revolves around the body (along with the detectors, in third-generation scanners), so that attenuation signal data may be acquired from multiple angular "views.” These data are pre-processed, filtered and back-projected to reconstruct an image of a cross-sectional slice through the body.
  • the body is translated axially relative to the plane of revolution of the tube, so that multiple image slices may be reconstructed, thereby producing a three-dimension CT image.
  • the quality of the CT image is dependent on the signal/noise ratio (SNR) of the attenuation data, which ratio generally increases with increasing radiation flux at the detectors, particularly when quantum fluctuations are the primary noise source. Therefore, the HVPS is commonly set to apply a relatively high current to the X-ray tube, resulting in a high X-ray flux irradiating the body. High flux is needed especially when imaging areas of the body in which a particularly high SNR is desired, such as the brain, or areas in which the X-ray attenuation is particularly high, such as the pelvis or shoulders, as well as in imaging the bodies of large subjects.
  • SNR signal/noise ratio
  • the X-ray attenuation may not be so high, so that acceptable SNR can be attained at a relatively lower X-ray flux.
  • the use of a higher X-ray flux than necessary is undesirable for several reasons: It exposes the subject to excessive radiation dosage, increases wear on the X-ray tube and HVPS, and adds to the cost of operating the CT scanner. Therefore, the X-ray flux should preferably be adjusted to account for the relative attenuation of the body.
  • the X-ray attenuation of the body increases with increasing body thickness, i.e., with increasing path length through the body. Because the cross-section of the torso is roughly elliptical, rather than circular, the path length of X-rays traversing the torso from side to side will be substantially greater than the path length from front to back. Therefore, the X-ray tube current that gives an irradiation level appropriate for views in which the tube is near the horizontal, so that the X-rays pass through the torso in the "thick" direction, will be greater than that needed for views in which the tube is near the vertical, in the "thin" direction.
  • X-ray attenuation along a given path depends not only on the path length through the body, but also on the types of tissues that the X-rays traverse along the path. Bone in particular attenuates X-rays much more strongly that soft tissue. Any method of compensating for thickness variations must take such differences into account.
  • the terms "thickness,” “thick” and “thin” used in reference to directions of radiation flux through the body refer to the combined effects of path length through the body and tissue type in determining directions of greater and lesser attenuation.
  • a method for optimally adjusting the flux during the scan, without the necessity of performing a preliminary planar scan.
  • the attenuation data from each axial image slice in the scan are used to adjust the flux during the next, successive image slice.
  • the attenuation data from each view or group of successive views are used to adjust the flux during the next view or group of views in succession.
  • the flux is adjusted so as to provide greater irradiation in a "thick" direction than in a "thin” direction.
  • the present invention further provides an apparatus for adjusting flux in a CT scanner as defined in claim 21 and a CT scanner as defined in claim 22.
  • a CT scanner acquires X-ray attenuation data from one or more initial view angles through the body of a subject, along the course of a CT scan path. These data are used to determine a modulation function for controlling the intensity of X-ray irradiation of the body as a function of view angle, so as to provide suitably greater flux in radial directions characterized by high attenuation ("thick") than in low-attenuation ("thin”) directions.
  • the CT scan continues, so that the scanner may acquire X-ray attenuation data from one or more subsequent view angles therealong, in proximity to the initial view angles.
  • the modulation function is applied to control the irradiation intensity at the subsequent view angles and is subsequently modified in response to the attenuation data acquired in these view angles. These steps are preferably repeated iteratively over a range of radial and axial positions.
  • the X-ray irradiation is provided by an X-ray tube revolving around the body.
  • the tube is driven by a HVPS, controlled by a computer, which varies the current output of the HVPS in response to the modulation function.
  • the computer calculates and/or updates the modulation function continually, simultaneously with the CT scan of the body.
  • the modulation is determined so that the SNR of the acquired data will be approximately constant over an entire revolution of the tube and/or so that the data will have a generally constant average signal level over the entire revolution.
  • the CT scanner operates in a sequential mode, wherein attenuation data are acquired from a plurality of angular views at each of a sequence of axial positions, while the body is held axially stationary at each successive position.
  • the plurality of angular views at each position covers a complete 360° scan around the body, or alternatively, a 180° scan, which scan is then used to reconstruct a planar image slice through the body at the position.
  • the data acquired at each of the axial positions are used to modify the modulation function to be applied at the next axial position in sequence.
  • the data acquired at each view or group of views at each of the positions are used to modify the modulation function at a succeeding view or group of views at the axial position.
  • the CT scanner operates in a helix mode, wherein the axial position of the body is advanced continuously as data are acquired from a succession of view angles, so that successive views describe a spiral pattern relative to the axis.
  • a starting value of the modulation function is preferably initially determined using data acquired from one or more views over a first portion of the spiral in the vicinity of the first axial position. Alternatively, the starting value may be estimated a priori . Thereafter, the function is modified continually as the scan proceeds, using data acquired from each view or group of views along the spiral in succession.
  • the function is modified every time data from a new view angle are acquired, spaced, for example, 1° apart.
  • the data acquired in each new view, or alternatively, in each new group of views, are used to determine the modulation function to be applied in the next view.
  • the function may be modified after every 360°, 180° or 90° revolutionary segment along the spiral, or after any other suitable angular segments.
  • the data acquired in each new segment are then used to modify the modulation function to be applied in a corresponding segment of the next revolution in the scan.
  • the X-ray intensity is generally not constant, but rather varies as a function of view angle within the segment.
  • the CT scanner includes a detector array, comprising a plurality of detector elements, which generate raw data signals indicative of X-ray attenuation. These raw data are pre-processed to produce normalized, corrected, logarithmic attenuation data, which are then filtered and back-projected to reconstruct image slices of the body.
  • the raw data are used in determining and/or modifying the modulation function, as described above.
  • pre-processing of the raw data is performed in real time, and the pre-processed data are used in determining and/or modifying the modulation function.
  • the data are preferably adjusted to account for the intensity of X-ray irradiation at which the data were acquired.
  • the slice is used to find the thick and thin dimensions of the body at that position. These dimensions are then used in determining and/or modifying the modulation function to be applied at the second axial position.
  • the body is positioned symmetrically with respect to a central axis of the CT scanner, and a sinusoidal or similar function of view angle is used to modulate the X-ray irradiation.
  • the modulation function is adjusted to account for asymmetry of the body or for non-symmetrical positioning of the body relative to the central axis.
  • the function may be derived empirically from the attenuation data, and need not have a predetermined analytical form, although an analytical function may, of course, be used.
  • an outline of the body is determined from the reconstructed image and is then used to eliminate from the calculation of the modulation function image artifacts from areas outside the body. If not corrected for, these image artifacts can distort the modulation function and thereby lead to an uneven SNR.
  • a method for adjusting radiation flux in a CT scanner including:
  • acquiring radiation attenuation data from the CT scan includes acquiring data from three or more radial view angles.
  • the method further includes:
  • the attenuation data are normalized and corrected for variations in detection efficiency before determining the modulation function.
  • the attenuation data are back-projected to produce an image slice, and image information from the slice is used in determining the modulation function.
  • acquiring radiation attenuation data includes acquiring attenuation data from a succession of view angles describing a revolutionary pattern relative to an axis of the body, and determining the modulation function includes dividing the revolutionary pattern into a plurality of successive angular sectors and updating the function in each sector.
  • dividing the revolutionary pattern into the plurality of angular sectors includes uniquely associating each successive view angle with a successive sector.
  • determining the modulation function includes using the radiation attenuation data acquired in each sector to calculate the modulation function for controlling the radiation flux in a succeeding, adjacent sector, more preferably by using the radiation attenuation values acquired in a first sector to calculate the modulation function in a succeeding sector that includes substantially the same range of radial angles with respect to the body as the first sector.
  • acquiring attenuation data from the succession of view angles describing the revolutionary pattern includes acquiring attenuation data from a succession of view angles describing a spiral pattern.
  • determining the modulation function dependent on view angle includes determining an analytical function including functional parameters derived from the attenuation data, or alternatively, determining a set of empirical values of the function derived from the attenuation data.
  • a method for adjusting radiation flux in a CT scanner including:
  • the method further includes:
  • advancing the radiation source includes advancing the source along a substantially helical scan path relative to the body.
  • irradiating the body from one or more view angles within any one of the angular sectors includes irradiating the body from a single view angle within the angular sector.
  • the attenuation data are normalized and corrected for variations in detection efficiency before determining the modulation function.
  • Scanner 20 comprises a bed 24, supported by a base 26, on which bed a subject 22 lies while his body is being imaged by the scanner.
  • Scanner 20 further comprises an X-ray tube 28, which irradiates subject 22, and a detector array 30, which receives X-rays from tube 28 and generates signals responsive to the attenuation of the X-rays in passing through the subject's body.
  • array 30 comprises one or more parallel rows of X-ray detector elements 23.
  • Tube 28 and array 30 are mounted on an annular gantry 32, so as to rotate about subject 22.
  • Bed 24 is advanced through gantry 32 along axis 34, which is preferably parallel to the long axis of the subject's body.
  • Tube 28 is driven by electrical current from high-voltage power supply (HVPS) 38.
  • HVPS high-voltage power supply
  • a system control unit 46 provides control signals and or data to HVPS 38, so that the current provided by the HVPS to tube 28 may be varied dynamically during a scan, as will be described below.
  • Control unit 46 which generally comprises a computer, also provides control signals to advance bed 24, rotate gantry 32 and perform other system functions, as will also be described below.
  • HVPS 38 is generally capable of supplying any voltage or current over an operating range of tube 28.
  • the HVPS is controlled to supply one of a limited number of calibrated voltage values within the range, for example, 90, 120 and 140 kV. Since each of these voltages will cause tube 28 to produce a different X-ray energy spectrum, scanner 20 is preferably calibrated to account for these differences.
  • the current supplied by HVPS 38 is varied, in accordance with the principles of the present invention, the voltage preferably remains substantially constant. The current may be similarly selected from a range of calibrated, discrete values, or it may be continuously varied.
  • Scanner 20 as pictured in Fig. 1 is of a type known in the art as a third-generation CT-scanner, characterized in that both tube 28 and detector array 30 revolve about subject 22. It will be appreciated, however, that the principles of the present invention, as will be further described below, are equally applicable to other types of CT scanners, in particular fourth-generation CT scanners, which include annular detector arrays that remain stationary, while the X-ray tube revolves about the subject. Furthermore, scanner 20 may be operated in either a 360° image reconstruction mode or in a 180° reconstruction mode, as are known in the art.
  • Scanner 20 may be operated in either a sequential mode or a helix mode.
  • bed 24 is held stationary, while tube 28 makes a complete, 360° revolution thereabout. Bed 24 is then advanced to another axial position, and the revolution is repeated.
  • tube 28 rotates and bed 24 advances simultaneously, so that the tube describes a generally spiral path around axis 34.
  • bed 24 moves with substantially constant velocity, so that the spiral path has a constant pitch.
  • axis 34 is preferably substantially perpendicular to the plane of revolution of tube 28. Alternatively, however, axis 34 may be angled relative to this plane, as is known in the art.
  • data acquisition circuitry 36 acquires a "view," i.e., the circuitry receives signals from each element 23 of array 30 responsive to X-ray attenuation along a ray from tube 28 to the element.
  • Image reconstruction circuitry 40 receives data from acquisition circuitry 36 and performs signal normalization and logarithm operations, as are known in the art, to derive a corrected X-ray attenuation value corresponding to each of elements 23.
  • these values are rebinned, as is known in the art, to rearrange them from a fan beam format to a parallel beam format.
  • Circuitry 40 then performs filtering and back-projection operations, as are known in the art, to reconstruct three-dimensional CT images of body 22.
  • these images are stored in image memory 42, displayed by display unit 44, and may be otherwise printed and/or processed.
  • Fig. 2A is a flow chart illustrating a method for regulating the current supplied by HVPS 38 to tube 28 as a function of the tube's position relative to body 22, in accordance with a preferred embodiment of the present invention, in the sequential scan mode.
  • Bed 24 is positioned relative to gantry 32 at an initial position, and attenuation data are acquired by array 30 while tube 28 is scanned through an angle of at least 180°+ ⁇ , where ⁇ is the fan angle of the X-ray beam received by array 30, and preferably through a complete 360° revolution.
  • These data are preprocessed, filtered and back-projected to reconstruct an image slice, as described above.
  • the filtering and back-projection steps are not shown in Fig. 2A, since they are not directly pertinent to calculating the modulation function, as will be described below.
  • raw image data acquired by array 30 are used to calculate a view-angle-dependent modulation function, as indicated by a solid arrow 60 in Fig. 2A.
  • a view-angle-dependent modulation function as indicated by a solid arrow 60 in Fig. 2A.
  • the level of current supplied by HVPS 38 to tube 28 at which the data were acquired is taken into account in calculating the function.
  • Bed 24 is then advanced to a second axial position and the above steps are repeated.
  • the modulation function is applied to HVPS 38, in order to modulate the current that the HVPS supplies to tube 28.
  • the function is determined so that for view angles of tube 28 that were characterized by relatively high attenuation at the initial axial position, as indicated by relatively weak detector signals, the current is increased, while for angles characterized by relatively low attenuation, the current is decreased.
  • the view angles characterized by relatively high attenuation will generally be in the "thick" direction. It will be appreciated, however, that in this and other preferred embodiments of the present invention, there is no need to measure geometrical dimensions of body 22 in order to determine the modulation function.
  • the above steps are repeated in order to re-calculate and, if necessary, modify the modulation function for use at the next axial position thereafter or in the next 180° of the scan.
  • a smoothing function is applied in recalculating the modulation function, in order to avoid sharp variations in modulation that may cause image artifacts to appear.
  • Various modulation functions may be used for modulating the current produced by HVPS 38.
  • Calculating the modulation function as described above in reference to Fig. 2A, comprises determining the appropriate values for I ave and ⁇ I to give suitable signal levels for all view angles.
  • modulation function Given by equation (1) assumes that cross-sections of the subject's body are approximately symmetrical and are centrally placed along axis 34. If it is determined that these conditions of symmetry are not satisfied, because the patient's body is tilted, for example, a phase angle may be added to the cosine term in the equation.
  • Other modulation functions including arbitrary, computer-generated functions of the view angle, may also be used, in order to more exactly complement the attenuation profile of body 22.
  • raw attenuation data from array 30 are used to calculate the modulation function
  • data generated by CT scanner 20 at other processing stages may alternatively be used for this purpose.
  • pre-processed data from data acquisition circuitry 36 are used in calculating the function.
  • the data are pre-processed in real time during the scan. Because the pre-processed data have been normalized and corrected for beam intensity and detector efficiency levels, a more optimal, precise modulation function may be determined in this way.
  • Fig. 2B is a flow chart schematically illustrating still another preferred embodiment of the present invention. This embodiment is similar to those described above with reference to Fig. 2A, except that CT image information, rather than the raw or pre-processed attenuation data, is used in calculating the modulation function.
  • image reconstruction circuitry 40 filters and back-projects the data to produce image slices during the scan at the initial and subsequent axial positions. Then, as indicated by arrow 64, information taken from each of these image slices is used to calculate the modulation function for the following axial position. For example, image slices may be used to measure the thickness of body 22 for various view-angle axes, as well as to identify the subject's bones in the image and adjust the modulation function for their location and thickness.
  • image information may be combined with raw and/or pre-processed attenuation data to calculate the modulation function.
  • the image information may be used to calculate an initial modulation function, which is subsequently updated on the basis of the attenuation data.
  • Fig. 3 is a flow chart illustrating another method for regulating the current supplied by HVPS 38 to tube 28 as a function of the tube's position relative to body 22, in accordance with preferred embodiments of the present invention applicable to CT scanning in the helix scan mode described above.
  • each 360° scanning revolution of tube 28 along the helical path described by the tube relative to bed 24, as the bed advances through the tube's plane of revolution is divided into N equal angular sectors, each with an angular extent of 360°/N.
  • N may be any suitable integer value, up to the number of angular views that are acquired in a 360° scan.
  • tube 28 scans an initial segment of the spiral. Attenuation data are received from array 30 and are used to calculate the modulation function, preferably according to one of the methods described above with reference to Fig. 2A.
  • a sector index J is initialized to zero.
  • Bed 24 advances, and tube 28 revolves, preferably continuously and at constant speeds, over a first sector.
  • the modulation function is applied to HVPS 38 to control the radiation flux emitted by tube 28 as a function of the scan angle.
  • Data acquired from array 30 in the first sector are pre-processed and used in image reconstruction, as described above. At the same time, these data are used to update and, as necessary, recalculate and correct the modulation function for the next sector.
  • the data acquired in each, Jth, sector of a given revolution are preferably used in real time to update and modify the modulation function to be applied to control the X-ray flux in the next, J+1, sector of the same scan. Further preferably, data acquired in the given revolution up to and including the Jth sector are compared with data from one or more previous revolutions, in order to calculate, by interpolation, for example, an optimal value to assign to the modulation function for the J+1 sector.
  • the modulation function for the J+1 sector can be determined from the Jth sector data alone. In either case, the number of sectors N is preferably large enough so that the relative variation of the modulation function from one sector to the next is small.
  • the modulation function then has an arbitrary, adaptively-varying functional form, which is preferably smoothed to eliminate sharp current variations in the HVPS, which could cause artifacts to appear in the resultant CT image.

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EP98900988A 1997-01-29 1998-01-26 Variable current ct scanning Expired - Lifetime EP0956744B1 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
IL120097 1997-01-29
IL12009797A IL120097A0 (en) 1997-01-29 1997-01-29 Variable current CT scanning
PCT/IL1998/000038 WO1998033361A1 (en) 1997-01-29 1998-01-26 Variable current ct scanning

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EP0956744A1 EP0956744A1 (en) 1999-11-17
EP0956744B1 true EP0956744B1 (en) 2002-12-18

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US (1) US6198789B1 (ja)
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JP (1) JP2001509048A (ja)
DE (1) DE69810271T2 (ja)
IL (1) IL120097A0 (ja)
WO (1) WO1998033361A1 (ja)

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WO1998033361A1 (en) 1998-07-30
US6198789B1 (en) 2001-03-06
DE69810271D1 (de) 2003-01-30
JP2001509048A (ja) 2001-07-10
IL120097A0 (en) 1997-04-15
EP0956744A1 (en) 1999-11-17
DE69810271T2 (de) 2003-08-28

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